|Número de publicación||US5695464 A|
|Tipo de publicación||Concesión|
|Número de solicitud||US 08/669,297|
|Número de PCT||PCT/FR1994/001549|
|Fecha de publicación||9 Dic 1997|
|Fecha de presentación||28 Dic 1994|
|Fecha de prioridad||29 Dic 1993|
|También publicado como||CA2179276A1, DE69421627D1, DE69421627T2, EP0737080A1, EP0737080B1, WO1995017914A1|
|Número de publicación||08669297, 669297, PCT/1994/1549, PCT/FR/1994/001549, PCT/FR/1994/01549, PCT/FR/94/001549, PCT/FR/94/01549, PCT/FR1994/001549, PCT/FR1994/01549, PCT/FR1994001549, PCT/FR199401549, PCT/FR94/001549, PCT/FR94/01549, PCT/FR94001549, PCT/FR9401549, US 5695464 A, US 5695464A, US-A-5695464, US5695464 A, US5695464A|
|Cesionario original||Zambon Group Spa|
|Exportar cita||BiBTeX, EndNote, RefMan|
|Citas de patentes (42), Citada por (47), Clasificaciones (14), Eventos legales (8)|
|Enlaces externos: USPTO, Cesión de USPTO, Espacenet|
The present invention involves a procedure for the controlled injection of liquid in a tube used in a system of the type comprising a source of liquid to be injected connected by way of an upstream part of the tube to a pump which acts by means of pressure exerted on the tube so as to inject the liquid deriving from the source of the liquid towards a downstream part of the tube, a rotary motor under continuous current to actuate the pump and obtain a quantity of liquid injected as a function of the angle at which the motor rotates, and a motor control unit, with the motor transmitting to the control unit pulses, the frequency of which is proportional to the angle through which the motor rotates.
More and more human diseases are treated using the injection of a medicamentous substance into the patient's body. Thus, in the treatment of diabetes, it is necessary to carry out regular injections of insulin to the patients. Other diseases such as cancer are also treated by means of the injection of medicamentous substances. However, regular injection via needle and syringe present numerous problems, such as the regularity with which the injections must be respected, and especially the problem raised by the cutaneous damage caused by the multiple injections given.
The solution was thus for the patient to have a continuous treatment using an infusion needle permanently positioned through the entry of the catheter implanted in the patient, usually by means of an implanted chamber connected to a pump.
The improvement provided by this technique was that the patient wore the pump on his person in a pocket, or attached to a belt. The pump, actuated by an electric motor, injects, in a continuous manner, the medicamentous substance into the catheter, and thus provides the chemotherapy necessary to the patient without having to carry out continual injections via needle and syringe.
Regardless of the mechanical system used by pumps for the injection of a medicamentous substance (peristaltic, nutation, fingers, cams . . . ), a continuous injection means a fragmentation of the volume to be delivered in small quantities, injected at regular intervals. This fragmentation technique is necessary, since the volumes injected are small for generally long durations, especially when it involves ambulatory and portable systems. In order to get close to continuous functioning, the process is always the same: the pump injects into the tube connected to the infusion needle a quantity of medicamentous substance called bolus, which is always identical, for example, 25 ul or 50 ul. Only the period of fragmentation may be modified so as to obtain a treatment over a longer or shorter period.
The above method has the advantage of requiring a relatively simple motor control management. However, it has the disadvantage that pharmacokinetic results are not always adapted to the treatment. In effect, since the minimal bolus is fixed, a small volume injection (50, 100 ml) of medicamentous substance having to be given over a long duration (4 or 5 days) necessarily requires long fragmentation periods. Thus, if the treatment requires an injection of 100 ml for 5 days, the theoretical flow is 0.83 ml/h or 13.88 ul/mn. However, since the system supplies a bolus of 50 ul, a period of 3 mn 36 sec is necessary, that is, the system will deliver 50 ul every 3 mn 36 sec.
This kind of control does not provide good results from the pharmaco-kinetic point of view, since the infusion leads to a considerable fluctuation in the concentration of the product injected between two injections, as is illustrated in FIG. 1. With each injection represented on the first graphic by pulses separated in time by a fragmentation period, the concentration of the medicamentous substance injected into the patient's organism increases up to a maximal concentration, Cmax. Subsequent to this injection and until the following injection, the concentration decreases to a minimal concentration, Cmin.
In order to decrease maximally the Cmax/Cmin ratio, it is necessary to provide injections as close together as is possible, and this requires the injection of smaller elementary boli, as well as a shorter fragmentation period. This can only be carried out using mechanical systems, of the "continuous kind", equipped with an elaborate control motor so as to obtain acceptable precision. As a function of the flows required, it is necessary to be able to vary the two parameters of bolus and fragmentation period, or only the bolus, if the period chosen is acceptable in all cases.
However, this type of control requires great precision at the time of each injection, which leads to the necessity of having available cumbersome equipment and complicated software (of the PID type), for control in position and/or in speed. Moreover, the equipment, by virtue of its being heavy and cumbersome, and the software, by virtue of its taking up much CPU time, are both large consumers of energy, and this is absolutely not adapted to ambulatory pumps which are not equipped with batteries for supplying the unit.
An initial aim of the invention is thus to provide a procedure for the injection of liquid in a tube which allows a distribution of the liquid which is patently homogeneous, with time, to be obtained.
Another aim of the invention is to provide a procedure which allows the control and regulation of the injection of liquid in a tube, using, at each period, a correction based partially on the quantity of liquid injected during the preceding period.
Yet another aim of the invention is to create a procedure for the injection of a medicamentous substance by means of an ambulatory pump which permits a ratio between the maximal concentration and minimal concentration of the substance in the patient's organism which is very close to one.
The object of the invention is thus a procedure characterised by the following stages, put to work each time the motor is started up: count the pulses transmitted by the motor and provide a signal of motor supply break when the number of pulses reaches a warning value of m, count the pulses transmitted by the motor between the supply break and its outage, add m+n and add to the total sum of pulses accumulated since the first motor start-up, subtract from this thus found sum a theoretical value equal to the product of a predetermined number by N, in order to obtain an algebraic error, and replace the warning value by a new value equal to the difference between the said predetermined number and a number equal to the sum of the algebraic error and a predetermined constant so that the algebraic error is approximately the same at each phase of motor functioning. In the preferred performance mode of the invention, the predetermined constant is defined as being the mean number .of pulses transmitted by the motor between the supply break and outage when the total number of pulses transmitted by the motor is equal to the said predetermined number.
The aims, objects and characteristics of the invention will be better understood upon reading the description which follows, made with reference to the drawings, in which FIG. 1 represents the diagrams in relation to the times of pulses of injection of a medicamentous substance and of the resulting concentration of substance in the patient's organism.
FIG. 2 represents, on a same diagram in relation to the time, the curves of the control motor, the pulses transmitted back by the motor, and motor speed.
FIG. 3 schematically represents an initial means of creating the invention using a microcontroller, and
FIG. 4 schematically represents a second means of creating the invention using a microprocessor.
As mentioned previously, one of the aims of the invention is to obtain a ratio of maximal and minimal concentrations (see FIG. 1) of the medicamentous substance in the patient's organism, one that will be closest to 1.
In order to achieve this result it is, a priori, useful to understand the functioning of a continuous current motor used for the control of the pump referenced in FIG. 2. Generally speaking, when the motor is in the phase of functioning represented by curve 1, it transmits coder pulses to the control unit.
As illustrated in curve III, when the motor is started up it accelerates until reaching its nominal speed, Vn, after a given time. It then remains at this nominal speed until supply is ceased. As of this cut-off, it decelerates until outage is complete. There is thus pulse transmission by the motor during the entire duration in which it is controlled, but also during its deceleration phase after supply break. In order to prevent the concentration of the medicamentous substance from getting too low, logic indicates that the fragmentation period must be decreased (see FIG. 1), at the same time that the quantity of medicamentous substance injected at each start-up of the motor also must be decreased. However, as has just been seen, referenced in FIG. 2, the motor presents a deceleration phase after the end of motor control, during which time the pump continues to inject the medicament, and this is impossible to know precisely, unless very sophisticated means are available, as has already been mentioned, and which are incompatible with a portable pump. The more one decreases the fragmentation period, the more one increases the frequency of motor start-up and the more one increases the precision error on the quantity injected due to the motor's deceleration phases.
The principle of the invention thus consists in controlling the duration of motor functioning upon each start-up, so as to compensate for the error previously accumulated, and this by virtue of the transmission of pulses (generated by an optical or magnetic coder) by the motor towards the control unit.
Firstly, determination of a short fragmentation period which prevents the concentration of the medicamentous substance from descending too low must be made. Generally speaking, it is necessary to choose this period well below the half-life of the substance injected. Knowing the total volume to be injected, the basal volume or bolus to be injected at each period is determined. This basal volume is easily converted into the number of pulses of the coder, since the volume delivered by each rotation of the motor, and thus the volume injected upon each pulse, is known. Thus, the number of theoretical pulses corresponding to motor functioning for each period of fragmentation is known. The procedure will therefore consist in rectifying, at the time of each motor start-up, the number of theoretical pulses of the control motor via the absolute error of the accumulated number of pulses, an error due to the period of motor deceleration, of which it is impossible to determine the duration with precision, in order to obtain a warning value (in number of pulses) of the motor control.
The following example will permit a better understanding of the principle of the invention. Supposing that the fragmentation period chosen for the treatment had permitted a determination of a theoretical number of 10 pulses, during which the motor must be controlled at each phase, N, of functioning,
the values of the different variables (warning value, relative error, absolute error . . . ) during the phases of functioning are shown in table I.
______________________________________Phase of 1 2 3 4 5 6 7 8functioning (n)warning value (Vn) 10 4 7 6 6 7 6 6phase number of 16 7 11 10 9 11 10 10pulses (Mn)relative error (en) 6 3 4 4 3 4 4 4accumulated 16 23 34 44 53 64 74 84number of pulses (Nn)absolute error (En) 6 3 4 4 3 4 4 4______________________________________
At each phase of functioning, the warning value is equal to 10 (theoretical number of the motor control), decreased by the error on the total number of pulses desired in order to respect chronotherapy. Thus, at phase 2, the error is 6 and therefore the warning value is 4. At phase 3, the error is 3, and the warning value is established at 7 . . . and so on. It is seen upon reading the table above that the accumulated error tends to stabilise at 4, or, more generally, between 3 and 5. Such an error corresponds, at the end of the treatment, to several hundreds of nanolitres, and thus is negligeable when compared to the 50 or 100 ml injected in toto. It should be noted that this error is directly linked to the moment of motor inertia, thus to the speed reached by the motor at the time of supply break from the motor.
Upon reading the figures in the example given below it is seen that the absolute error is in fact equal to the relative error (number of pulses sent by the motor during the deceleration phase).
This is due to the fact that:
if Nn is the number of pulses accumulated in phase n,
Vn is the warning value and en is the relative error in phase n,
the number of accumulated pulses in phase n is equal to:
Nn =Nn-1 +Vn +en
and thus the absolute error in phase n is equal to
En =Nn -(10)(n)
En =Nn-1 +Vn +en -(10)(n)
and as at each phase the new wanting value is calculated by subtracting from 10 the preceding absolute error, that is:
Vn =10- Nn-1 -(10)(N-1)!
from which the conclusion is
Thus, at each phase the absolute error is equal to the relative error, that is, to the number of pulses in the motor's deceleration phase.
As has been previously mentioned, the number of pulses sent by the motor is not a value which can be determined with certainty. It is nonetheless possible to know the approximate value. For this reason, the procedure which has just been described can be improved by introducing a corrective value, predetermined in the calculation of the warning value. The warning value is, at each phase, equal to the theoretical number of pulses decreased from the preceding absolute error to which is added a predetermined constant permitting a total number of pulses to be obtained (Y comprises the deceleration phase)), approximately equal to the theoretical number. Thus, still within the hypothesis of a theoretical value of 10 pulses at each phase of functioning and considering a corrective constant of 4, the values of the different variables (warning value, relative error, absolute error . . . ) during the functioning phases are shown in table II which follows.
______________________________________Phase of functioning (n) 1 2 3 4 5 6 7 8warning value (Va) 6 6 5 7 6 6 5 7Phase number of pulses 10 11 8 11 10 11 8 11relative error (en) 4 5 3 4 4 5 3 4number accumulated 10 21 29 40 50 61 69 80of pulses (Nn)absolute error (En) 0 1 -1 0 0 1 -1 0______________________________________
Here again, it is interesting to calculate the absolute error in order to note that it is directly deducted from the relative error.
If Nn is the number of accumulated pulses in phase n, Vn is the warning value and en is the relative error relating to phase n; the number of accumulated pulses at phase n is equal to:
Nn =Nn +Vn +en
and thus the absolute error at phase n is equal to:
En =Nn -(10)(n)
En =Nn-1 +Vn +en -(10)(n)
and as at each phase the new warning value Vn is calculated by subtracting from 10 the previously increased warning value Vn decreased by the above mentioned corrective constant, 4 which equals, that is:
Vn =10- Nn-1 -10·(n-1)!-4
Vn =10·n-Nn-1 -4
One thus notes that it again suffices to consider the relative error of the preceding phase in order to calculate the warning value for each phase, except for the initial phase where the warning value is equal to the number of theoretical pulses decreased from the predetermined constant.
In order to improve the procedure, one may envisage having several motor supply voltages which can be selected, permitting a broader range of use. In effect, the lower the pressure is, the less the error is marked, due to a lower nominal speed.
In the invention's preferred performance mode, the continuous current motor supplies, under 5V controls, the pump with a reduction of 1/27, and an optical coder supplying 16 pulses per motor rotation.
With the characteristics of the pump, such as the quantity of liquid injected at each rotation of the pump, that is, 25 ul, the quantity injected at each pulse is 25 ul/27×16=57.87 nl.
If a fragmentation period of 5s is chosen, that is, if the motor is started up every 5s, and taking a theoretical number of pulses which is equal to 10 at each phase of operation, the quantity of medicamentous substance injected per hour will be:
57.87 nl×10×720=416.66 ul
With the same pump, but by chosing a theoretical number of pulses which is equal to 20, an hourly quantity of 883.32 ul is obtained. Thus, with a same fragmentation period, but by choosing a different theoretical number of pulses, it is possible to adapt the chronotherapy depending on the kind of treatment desired.
The invention procedure can be implemented in a general manner by means of the system illustrated in FIG. 3. The control unit is a micro-controller providing supply V to motor 12 via switch 14. The micro-controller keeps in the memory the value of the theoretical number of pulses Vn to be delivered to each phase of motor operation. At the start-up of an operational phase, the microcontroller sends a validation signal to line 16 to close switch 14 and supply motor 12. The coder, 18, transmits pulses Mn back to the micro-controller 10. The former are discounted from the warning value up to value O. At this value, the micro-controller stops transmitting the validation signal on line 16, and the motor, 12, is no longer supplied. During the deceleration phase, the pulses transmitted by coder 18 are counted in order to determine the relative error en which will serve to calculate the absolute error En and the new warning value Vn to be applied at the time of the following phase of operation.
The invention's preferred performance mode can be carried out by the system illustrated in FIG. 4. In this concept, the control unit is simply a microprocessor 20. As previously, the supply voltage is supplied to motor 22 via the intermediary of a switch, 24. A counter/discounter (+/- measurement control), 26, receives from/or transmits its data to the microprocessor, 20, by means of an 8 byte bus, 28, with reading control of decoding taking place by means of the control lines, 30. At the start-up of a phase of motor functioning, the warning value Vn equal to a decreased theoretical number of pulses of a predetermined corrective constant is loaded into the counter/discounter (+/- measurement control) 26. The exit, 32, of the latter is actuated only when the counter is empty and thus is at 0, and 1 is supplied at the exit of the inverter, 34, which has the effect of closing the switch, 24, allowing supply to the motor, 22. Consequently, the coder, 36, transmits pulses. By virtue of the fact that the exit of the inverter, 34, is at 1, gateway ET5 38 allows passage, whilst gateway ET 40, receiving 0 at the exit of line 32 is blocked. The pulses transmitted by coder 36 are thus supplied, via circuit ET 38 at the entry of DEC counting of the counter/discounter (+/- measurement control) 26. When the counter/discounter (+/- measurement control) 26 reaches value 0, a signal, 1, is sent to line 32, which renders gateway ET 40 passable, but blocks gateway ET 38 by virtue of the fact that the exit of inverter 34 opens switch 24 and cuts the supply of motor 22. The pulses provided by coder 36 during the motor's deceleration phase are thus transmitted, via gateway ET 40, to the entry of COM counting of the counter/discounter (+/- measurement control) 26. At the end of the deceleration phase, the value reached by counter 26 read by microprocessor 20, by means of bus 28, is subtracted from the theoretical number of pulses (10 in the examples given above, so as to obtain the new warning value to be loaded onto the counter/discounter (+/- measurement control) 26 at the start-up of the following phase.
The software necessary to implement the invention procedure in the system illustrated in FIG. 4 is very simple. In effect, one begins by providing the system constants, that is:
the volume injected by motor rotation
the number of pulses per motor rotation
From these constants the software easily determines, as a function of the treatment duration and the total volume to be delivered during the treatment, the number of pulses to be generated at each period or warning value, that is:
NPP: number of pulses per period
The software is then simply made up of the following instructions, carried out at each phase of motor operation:
reading of the counter→ERR
reset of counter at zero
calculation of NPP-ERR=VAL (warning value)
Loading of VAL into the discounter (-measurement control)
If the warning value is decreased in the initial phase by a corrective value with a view to decreasing the error value as has been mentioned previously, it is necessary to establish the flow value of the variable NPP not equal to the number of pulses to be obtained per period, but to this decreased number of the corrective value.
In order to improve the procedure established by the system illustrated in FIG. 4, it is possible to join to it a self-adaptating software. In effect, due to the fact that the parameters may be different depending on the application (large flow, small flow . . . ) and that the components used (silicone tube, motor, reduction ratio . . . ) may be different, a motor response represented by a number of pulses following supply break which is different depending on the cases is obtained.
The self-adaptation software comprises firstly a learning sequence during which the number of pulses generated following supply break of the motor or the progressive warning values is determined.
______________________________________Warning value Number of pulses during deceleration______________________________________ 1 pulse n1 10 pulses n10 50 pulses n50100 pulses n100200 pulses n200500 pulses n500______________________________________
The value ni is determined by a number, i, of pulses sufficient for the motor to reach its nominal speed. The number of maximal pulses may be 200, 500 or even 1000.
Subsequently, starting with values n1, n10, n50 . . . the software makes a linear interpolation for each pair of 2 successive warning values in order to determine a number, n, for any warning value whatsoever.
The values, ni, which were thus determined are used during an infusion in order to determine the constant to be subtracted from the theoretical warning value so as arrive at the real warning value to be applied at each phase of motor operation.
However, a third phase of software self-adaptation may also be foreseen and it consists in establishing a table in which the warning value to be applied by subtracting from the theoretical warning value the number of corresponding pulses obtained during the learning sequence of the software is determined. Thus, the table obtained will contain the relative error value to be applied for each theoretical warning value, as it appears in table II above.
Although in the preferred performance mode the invention's procedure is partially implemented using software (in the microprocessor in FIG. 4) and partially via the equipment, it is in the hands of the professional to implement this procedure using only logical circuits. However, given the progress in making semiconducting devices miniature, it is more prudent to use the power of a microprocessor to carry out some functions with the help of software.
|Patente citada||Fecha de presentación||Fecha de publicación||Solicitante||Título|
|US3623474 *||25 Jul 1966||30 Nov 1971||Medrad Inc||Angiographic injection equipment|
|US3701345 *||29 Sep 1970||31 Oct 1972||Medrad Inc||Angiographic injector equipment|
|US3858581 *||2 Jul 1973||7 Ene 1975||Dean Kamen||Medication injection device|
|US4037598 *||12 Ago 1974||26 Jul 1977||Ivac Corporation||Method and apparatus for fluid flow control|
|US4111198 *||2 Jun 1977||5 Sep 1978||Alvin J. Marx||Automated intravenous fluid regulating and administering apparatus|
|US4137913 *||28 Feb 1975||6 Feb 1979||Ivac Corporation||Fluid flow control system|
|US4150672 *||12 Nov 1976||24 Abr 1979||Martin John K||Injection device and method|
|US4294248 *||16 Oct 1979||13 Oct 1981||Figueiredo Nuno R M De||Device for automatically controlling the infusion liquid flow in an infusion apparatus|
|US4367435 *||15 Dic 1980||4 Ene 1983||Ivac Corporation||Motor control system|
|US4396385 *||5 Dic 1980||2 Ago 1983||Baxter Travenol Laboratories, Inc.||Flow metering apparatus for a fluid infusion system|
|US4397639 *||23 Abr 1981||9 Ago 1983||Ferring Arzneimittel Gmbh||Device for the intermittent pulsatory application of fluid medicaments|
|US4405318 *||27 Mar 1981||20 Sep 1983||Whitney Douglas S G||Injector with ratchet drive and reproducing system|
|US4432468 *||6 Feb 1981||21 Feb 1984||Siff Elliott J||Intravenous delivery system|
|US4468219 *||20 Dic 1983||28 Ago 1984||International Business Machines Corporation||Pump flow rate compensation system|
|US4475666 *||31 Ago 1981||9 Oct 1984||American Hospital Supply Corporation||Automated liquid dispenser control|
|US4498843 *||2 Ago 1982||12 Feb 1985||Schneider Philip H||Insulin infusion pump|
|US4600401 *||18 Oct 1983||15 Jul 1986||Baxter Travenol Laboratories||Fluid flow control system|
|US4731057 *||30 Jul 1986||15 Mar 1988||Nikkiso Co., Ltd.||Transfusion apparatus|
|US4731058 *||22 May 1986||15 Mar 1988||Pharmacia Deltec, Inc.||Drug delivery system|
|US4778450 *||6 Jun 1986||18 Oct 1988||Baxter Travenol Laboratories, Inc.||Fluid flow control system|
|US4838860 *||26 Jun 1987||13 Jun 1989||Pump Controller Corporation||Infusion pump|
|US4840620 *||3 Abr 1987||20 Jun 1989||Terumo Corporation||Portable pump for infusing medicine into a living body|
|US4850805 *||13 Mar 1987||25 Jul 1989||Critikon, Inc.||Pump control system|
|US4898579 *||3 Jun 1988||6 Feb 1990||Pump Controller Corporation||Infusion pump|
|US4919596 *||26 Abr 1989||24 Abr 1990||Pacesetter Infusion, Ltd.||Fluid delivery control and monitoring apparatus for a medication infusion system|
|US4919650 *||29 Mar 1988||24 Abr 1990||Bionica Pty. Limited||Infusion pump|
|US4985015 *||23 Nov 1988||15 Ene 1991||Siemens Aktiengesellschaft||Dosing device for controlled injection of liquid from a reservoir into an organism|
|US4988337 *||8 Ago 1989||29 Ene 1991||Terumo Kabushiki Kaisha||Syringe pump apparatus|
|US5181910 *||28 Feb 1991||26 Ene 1993||Pharmacia Deltec, Inc.||Method and apparatus for a fluid infusion system with linearized flow rate change|
|US5219330 *||26 Nov 1991||15 Jun 1993||Imed Corporation||Method and apparatus for preprogrammed infusion of iv medicaments|
|US5256157 *||10 Dic 1992||26 Oct 1993||Baxter International Inc.||Automated infusion pump with replaceable memory cartridges|
|US5318521 *||30 Abr 1993||7 Jun 1994||Siemens Aktiengesellschaft||Dosing device for the controlled delivery of a liquid|
|US5320503 *||23 Sep 1993||14 Jun 1994||Patient Solutions Inc.||Infusion device with disposable elements|
|US5389078 *||6 Oct 1993||14 Feb 1995||Sims Deltec, Inc.||Programmable infusion pump for administering medication to patients|
|US5425716 *||10 Ago 1992||20 Jun 1995||Atom Kabushiki Kaisha||Infusion apparatus|
|US5442267 *||14 Jun 1993||15 Ago 1995||Mita Industrial Co., Ltd.||Device for controlling the reverse rotation of a motor and method of judging time point where the motor is actually rotated in a reverse direction|
|US5463293 *||25 Ene 1994||31 Oct 1995||Nec Corporation||Motor control device|
|US5534691 *||12 Sep 1994||9 Jul 1996||Ivac Corporation||System for determining pumping mechanism position while limiting volume of fluid pumped|
|US5584667 *||6 Jun 1995||17 Dic 1996||Davis; David L.||Method of providing uniform flow from an infusion device|
|US5609576 *||13 Sep 1994||11 Mar 1997||Ivac Medical Systems, Inc.||Fluid flow impedance monitoring system|
|EP0039044A1 *||22 Abr 1981||4 Nov 1981||Ferring Biotechnik GmbH||Intermittent delivery system for a medical liquid|
|EP0285403A2 *||30 Mar 1988||5 Oct 1988||Bionica Pty. Limited||Infusion pump|
|Patente citante||Fecha de presentación||Fecha de publicación||Solicitante||Título|
|US5925022 *||10 Nov 1998||20 Jul 1999||Liebel-Flarsheim Company||Medical fluid injector|
|US6159183 *||10 Nov 1999||12 Dic 2000||Liebel Flarsheim Company||Medical fluid injector having face plate with magnetic conductors|
|US6285155||29 Oct 1999||4 Sep 2001||Abbott Laboratories||Pseudo half-step motor drive method and apparatus|
|US6299600 *||29 Jun 2000||9 Oct 2001||Jms Co., Ltd.||Liquid pump|
|US6485471||3 Mar 2000||26 Nov 2002||Roche Diagnostics Corporation||Bellowed fluid delivery apparatus|
|US6558351 *||1 Jun 2000||6 May 2003||Medtronic Minimed, Inc.||Closed loop system for controlling insulin infusion|
|US7267665||31 Dic 2002||11 Sep 2007||Medtronic Minimed, Inc.||Closed loop system for controlling insulin infusion|
|US7402153||31 Mar 2004||22 Jul 2008||Medtronic Minimed, Inc.||Closed-loop method for controlling insulin infusion|
|US7500959 *||4 Oct 2001||10 Mar 2009||Novo Nordisk A/S||Medication delivery system with improved dose accuracy|
|US7547281||30 Dic 2005||16 Jun 2009||Medtronic Minimed, Inc.||Algorithm sensor augmented bolus estimator for semi-closed loop infusion system|
|US7946985||29 Dic 2006||24 May 2011||Medtronic Minimed, Inc.||Method and system for providing sensor redundancy|
|US7985330||29 Dic 2006||26 Jul 2011||Medtronic Minimed, Inc.||Method and system for detecting age, hydration, and functional states of sensors using electrochemical impedance spectroscopy|
|US8105268||19 Oct 2010||31 Ene 2012||Medtronic Minimed, Inc.||Safety limits for closed-loop infusion pump control|
|US8105269||24 Oct 2008||31 Ene 2012||Baxter International Inc.||In situ tubing measurements for infusion pumps|
|US8114268||21 Ago 2007||14 Feb 2012||Medtronic Minimed, Inc.||Method and system for remedying sensor malfunctions detected by electrochemical impedance spectroscopy|
|US8114269||28 Dic 2007||14 Feb 2012||Medtronic Minimed, Inc.||System and method for determining the point of hydration and proper time to apply potential to a glucose sensor|
|US8137083||11 Mar 2009||20 Mar 2012||Baxter International Inc.||Infusion pump actuators, system and method for controlling medical fluid flowrate|
|US8287495||10 Oct 2011||16 Oct 2012||Tandem Diabetes Care, Inc.||Infusion pump system with disposable cartridge having pressure venting and pressure feedback|
|US8298184||30 Oct 2012||Tandem Diabetes Care, Inc.||Infusion pump system with disposable cartridge having pressure venting and pressure feedback|
|US8382447||31 Dic 2009||26 Feb 2013||Baxter International, Inc.||Shuttle pump with controlled geometry|
|US8408421||29 Oct 2008||2 Abr 2013||Tandem Diabetes Care, Inc.||Flow regulating stopcocks and related methods|
|US8448824||26 Feb 2009||28 May 2013||Tandem Diabetes Care, Inc.||Slideable flow metering devices and related methods|
|US8454576||6 Feb 2012||4 Jun 2013||Medtronic Minimed, Inc.||Device and method for therapy calibration and safety response|
|US8496613||30 Ene 2012||30 Jul 2013||Baxter International Inc.||In situ tubing measurements for infusion pumps|
|US8567235||29 Jun 2010||29 Oct 2013||Baxter International Inc.||Tube measurement technique using linear actuator and pressure sensor|
|US8608924||16 Dic 2011||17 Dic 2013||Medtronic Minimed, Inc.||System and method for determining the point of hydration and proper time to apply potential to a glucose sensor|
|US8650937||18 Sep 2009||18 Feb 2014||Tandem Diabetes Care, Inc.||Solute concentration measurement device and related methods|
|US8679016||13 Abr 2011||25 Mar 2014||Medtronic Minimed, Inc.||Method and system for providing sensor redundancy|
|US8708993 *||24 Sep 2004||29 Abr 2014||Physician Technologies, Inc.||Infusion catheter procedure and system|
|US8758323||29 Jul 2010||24 Jun 2014||Tandem Diabetes Care, Inc.||Infusion pump system with disposable cartridge having pressure venting and pressure feedback|
|US8784370||15 Dic 2011||22 Jul 2014||Medtronic Minimed, Inc.||Safety limits for closed-loop infusion pump control|
|US8926561||29 Jul 2010||6 Ene 2015||Tandem Diabetes Care, Inc.||Infusion pump system with disposable cartridge having pressure venting and pressure feedback|
|US8986253||7 Ago 2009||24 Mar 2015||Tandem Diabetes Care, Inc.||Two chamber pumps and related methods|
|US9211377||29 Jul 2010||15 Dic 2015||Tandem Diabetes Care, Inc.||Infusion pump system with disposable cartridge having pressure venting and pressure feedback|
|US20020107486 *||4 Oct 2001||8 Ago 2002||Munk Jens Aage||Medication delivery system with improved dose accuracy|
|US20030130616 *||31 Dic 2002||10 Jul 2003||Medtronic Minimed, Inc.||Closed loop system for controlling insulin infusion|
|US20040193025 *||31 Mar 2004||30 Sep 2004||Medtronic Minimed, Inc.||Closed-loop method for controlling insulin infusion|
|US20060173406 *||30 Dic 2005||3 Ago 2006||Medtronic Minimed, Inc||Algorithm sensor augmented bolus estimator for semi-closed loop infusion system|
|US20070170073 *||29 Dic 2006||26 Jul 2007||Medtronic Minimed, Inc.||Method and System for Detecting Age, Hydration, and Functional States of Sensors Using Electrochemical Impedance Spectroscopy|
|US20080161664 *||29 Dic 2006||3 Jul 2008||Medtronic Minimed, Inc.||Method and System for Providing Sensor Redundancy|
|US20080188796 *||4 Abr 2008||7 Ago 2008||Medtronic Minimed, Inc.||Closed-Loop Method for Controlling Insulin Infusion|
|US20080269723 *||25 Abr 2007||30 Oct 2008||Medtronic Minimed, Inc.||Closed loop/semi-closed loop therapy modification system|
|US20090043291 *||26 Sep 2008||12 Feb 2009||Medtronic Minimed, Inc.||Closed Loop Medicament Pump|
|US20090048584 *||26 Sep 2008||19 Feb 2009||Medtronic Minimed, Inc.||Closed Loop Medicament Pump|
|US20110218489 *||8 Sep 2011||Medtronic Minimed, Inc.||Method and System for Providing Sensor Redundancy|
|US20120265127 *||18 Oct 2012||Thomas Buri||Occlusion recognition in an administering apparatus|
|EP1092440A1 *||1 Jul 1999||18 Abr 2001||JMS Co., Ltd.||Liquid pump|
|Clasificación de EE.UU.||604/67, 604/154, 604/131, 604/65, 128/DIG.1, 604/151, 128/DIG.12|
|Clasificación internacional||A61M5/142, A61M5/172, A61M5/00|
|Clasificación cooperativa||Y10S128/12, Y10S128/01, A61M5/172|
|30 Ago 1996||AS||Assignment|
Owner name: ZAMBON GROUP SPA, ITALY
Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:VIALLET, FABIEN;REEL/FRAME:008202/0681
Effective date: 19960817
|11 Jun 2001||FPAY||Fee payment|
Year of fee payment: 4
|29 Jun 2005||REMI||Maintenance fee reminder mailed|
|6 Dic 2005||SULP||Surcharge for late payment|
Year of fee payment: 7
|6 Dic 2005||FPAY||Fee payment|
Year of fee payment: 8
|15 Jun 2009||REMI||Maintenance fee reminder mailed|
|9 Dic 2009||LAPS||Lapse for failure to pay maintenance fees|
|26 Ene 2010||FP||Expired due to failure to pay maintenance fee|
Effective date: 20091209